Muscle activity monitoring

ABSTRACT

A system for monitoring muscle activity of a biological subject, the system including at least one garment including a number of arrays of electrodes positioned on the garment so that when the garment is worn by a subject in use, the electrodes contact skin of the subject and generate electrical signals indicative of electrical potentials within respective muscles of the subject and at least one electronic processing device that processes signals from the electrodes in each electrode array to determine a muscle activation for parts of the respective muscles and uses the muscle activation to determine at least one muscle indicator indicative of muscle activity of the subject.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.15/560,476, filed Sep. 21, 2017, now pending, which application is aU.S. National Stage of International Application No. PCT/AU2016/050203,filed Mar. 22, 2016, which claims the benefit of and priority toAustralian Patent Application No. 2015901026, filed Mar. 23, 2015, thecontents of each of which are hereby incorporated by reference in theirentireties.

BACKGROUND OF THE INVENTION

The present invention relates to a system and method for monitoring themuscle activity of a subject, and in particular to a system formonitoring muscle activity of a subject using at least one garment wornby the subject in use.

DESCRIPTION OF THE PRIOR ART

The reference in this specification to any prior publication (orinformation derived from it), or to any matter which is known, is not,and should not be taken as an acknowledgment or admission or any form ofsuggestion that the prior publication (or information derived from it)or known matter forms part of the common general knowledge in the fieldof endeavour to which this specification relates.

Whilst it is known to provide devices for monitoring activity, these aregenerally limited to detecting movement through the use of movementsensors, which does not accurately track muscle activity. Measuringmuscle activity by recording electrical signals from muscles, in aprocess commonly referred to as EMG (Electromyography) is known, thisgenerally uses needle electrodes inserted into the muscles of thesubject, which is therefore restrictive and therefore only used inlimited situations.

SUMMARY OF THE PRESENT INVENTION

In one broad form the invention seeks to provide a system for monitoringmuscle activity of a biological subject, the system including:

a) at least one garment including a number of arrays of electrodespositioned on the garment so that when the garment is worn by a subjectin use, the electrodes contact skin of the subject and generateelectrical signals indicative of electrical potentials within respectivemuscles of the subject; and,

-   -   b) at least one electronic processing device that:

i) processes signals from the electrodes in each electrode array todetermine a muscle activation for parts of the respective muscles; and,

ii) uses the muscle activation to determine at least one muscleindicator indicative of muscle activity of the subject.

In another broad form the invention seeks to provide a method formonitoring muscle activity of a biological subject, the methodincluding:

-   -   a) providing the subject with at least one garment including a        number of arrays of electrodes positioned on the garment so that        when the garment is worn by the subject, the electrodes contact        skin of the subject and generate electrical signals indicative        of electrical potentials within respective muscles of the        subject; and,    -   b) in at least one electronic processing device:        -   i) processing signals from the electrodes in each electrode            array to determine a muscle activation for parts of the            respective muscles; and,        -   ii) using the muscle activation to determine at least one            muscle indicator indicative of muscle activity of the            subject.

In another broad form the invention seeks to provide a garment for usein monitoring muscle activity of a biological subject, the garmentincluding a number of arrays of electrodes positioned on the garment sothat when the garment is worn by a subject in use, the electrodescontact skin of the subject and generate electrical signals indicativeof electrical potentials within respective muscles of the subject.

Typically the muscle activation is indicative of at least one of amagnitude and frequency of muscle activation.

Typically the muscle indicator includes at least one of:

-   -   a) an intramuscular indicator indicative of muscle activation        within a muscle;    -   b) an intermuscular indicator indicative of a relative muscle        activation of contralateral muscles on contralateral limbs;    -   c) an efficiency indicator indicative of the relative efficiency        of muscle activation of muscles; and,    -   d) a muscle fatigue indicator indicative of a muscle fatigue.

Typically the at least one processing device, for each muscle:

-   -   a) determines an average muscle activation;    -   b) compares the muscle activation of parts of the muscle to the        average muscle activation; and,    -   c) determines an intramuscular indicator at least in part using        results of the comparison.

Typically the at least one processing device, for each pair ofcontralateral muscles:

-   -   a) compares the muscle activation of each muscle in the pair;        and,    -   b) determines an intermuscular indicator at least in part using        results of the comparison.

Typically the at least one processing device:

-   -   a) determines a muscle activation pattern indicative of the        muscle activation of each of a number of muscles;    -   b) compares the muscle activation pattern to a reference muscle        activation pattern; and,    -   c) determines an efficiency indicator at least in part using the        results of the comparison.

Typically the at least one processing device:

-   -   a) determines an activity being performed by the subject; and,    -   b) selects one of a number of predefined reference activation        patterns at least partially in accordance with the determined        activity.

Typically the at least one processing device determines the activitybeing performed at least one of:

-   -   a) by analysing muscle activation patterns; and,    -   b) in accordance with user input commands.

Typically the at least one processing device selects one of a number ofpredefined reference activation patterns in accordance with subjectparameters including at least one of:

-   -   a) a subject age;    -   b) a subject sex;    -   c) a subject weight;    -   d) a subject height; and,    -   e) a subject fitness level.

Typically the predefined reference activation patterns include aprevious recorded activation pattern for the subject.

Typically the at least one processing device:

-   -   a) determines a current muscle activation pattern indicative of        the muscle activation of each of a number of muscles;    -   b) determines previous muscle activation patterns;    -   c) identifies a historical activation based on at least one of a        mean and maximum of the previous muscle activation patterns;    -   d) compares the current muscle activation pattern to the        historical activation pattern; and,    -   e) determines a fatigue indicator at least in part using the        results of the comparison.

Typically the at least one processing device:

-   -   a) generates a representation at least partially based on the at        least one muscle indicator; and,    -   b) causes the representation to be displayed to a user.

Typically the representation includes at least one of:

-   -   a) an alphanumeric indication of the at least one muscle        indicator;    -   b) a graphical representation of a muscle activation pattern for        at least one muscle; and,    -   c) a graphical representation of results of a comparison of a        muscle activation pattern to a reference muscle activation        pattern.

Typically the electrodes are at least one of:

-   -   a) conductive fabric electrodes woven into the garment; and,    -   b) dry electrodes provided in the garment.

Typically the electrodes are at least one of:

-   -   a) silver plated nylon electrodes; and,    -   b) silver plated nanowire electrodes.

Typically each array of electrodes includes a plurality of electrodesarranged in a grid.

Typically each electrode has a surface area that is at least one of:

-   -   a) between 0.5 cm² and 3.0 cm²;    -   b) between 0.75 cm² and 1.5 cm²;    -   c) about 0.75±0.25 cm²;    -   d) about 1.0±0.25 cm²;    -   e) about 1.25±0.25 cm²;    -   j) about 1.5±0.25 cm²;    -   g) about 1.75±0.25 cm²;    -   h) about 2.0±0.25 cm²;    -   i) about 2.5±0.5 cm²; and,    -   j) about 1 cm².

Typically electrodes in the array are spaced by at least one of:

-   -   a) between 0.5 cm and 2.0 cm;    -   b) between 0.75 cm and 1.75 cm;    -   c) between 1.0 cm and 1.5 cm;    -   d) about 0.75±0.25 cm;    -   e) about 1.0±0.25 cm;    -   f) about 1.25±0.25 cm; and,    -   g) about 1.5±0.25 cm.

Typically each electrode in the electrode array is electricallyconnected to a connector, the connector being for coupling theelectrodes to the at least one processing device.

Typically at least one processing device is mounted in a pocket providedon the garment, the connector being provided at least partially withinthe pocket.

Typically each electrode in the electrode array is electricallyconnected to the connector via nanowires woven into the garment.

Typically the garment includes at least one of:

-   -   a) pants for covering at least the groin and upper legs of the        user; and,    -   b) a shirt for covering at least the torso of the user.

Typically the garment includes elasticated material to thereby urge theelectrodes against the subject's skin.

Typically the garment is made of at least one of:

-   -   a) polyamides;    -   b) polyester; and,    -   c) elastane.

Typically each array of electrodes is aligned with a respective muscleor muscle group.

Typically the muscle or muscle groups include at least one of:

-   -   a) trapezius;    -   b) rhomboids;    -   c) latissimus dorsi;    -   d) erector spinae;    -   e) rotator cuff muscles (including supraspinatus, infraspinatus,        subscapularis, teres minor/major); f) forearm extensors/flexors;    -   g) tibialis anterior/posterior;    -   h) thoracic paraspinals;    -   i) lumbar paraspinals;    -   j) biceps;    -   k) triceps;    -   l) quadriceps;    -   m) hamstrings;    -   n) adductors;    -   o) gluteals;    -   p) calves;    -   q) abdominals;    -   r) deltoids; and,    -   s) pectorals.

Typically system includes a measuring device, the measuring deviceincluding:

-   -   a) a voltage sensor coupled to the electrodes for sensing        electrical potentials between pairs of electrodes; and,    -   b) at least one processing device coupled to the voltage sensor        for receiving signals indicative of the sensed voltages.

Typically the voltage sensor includes:

-   -   a) a differential amplifier for amplifying analogue electrical        signals obtained from a pair of electrodes; and,    -   b) an A/D convertor for converting an amplified differential        voltage into a digital voltage signal, the digital voltage        signal being provided to the at least one processing device for        processing.

Typically the measuring device includes a filter for filteringelectrical signals.

Typically the measuring device includes a switching device forselectively coupling the voltage sensor to respective pairs ofelectrodes in each array.

Typically the switching device is controlled at least in part by the atleast one processing device.

Typically the system includes:

-   -   a) a first electronic processing device attached to or worn by        the subject that:        -   i) acquires signals from the sensors;        -   ii) at least partially processes the signals; and,    -   b) a second processing device that wirelessly communicates with        the first processing device and displays a representation at        least partially based on the at least one muscle indicator.

Typically the system includes an ECG sensor for sensing cardiac activityof the subject and wherein the at least one electronic processingdevice:

-   -   a) acquires signals from the ECG sensor; and,    -   b) determines a cardiac indicator indicative of cardiac activity        of the subject.

Typically the system includes a respiratory sensor for sensingrespiratory activity of the subject and wherein the at least oneelectronic processing device:

-   -   a) acquires signals from the respiratory sensor; and,    -   b) determines a respiratory indicator indicative of respiratory        activity of the subject.

Typically the at least one electronic processing device determines anactivity indicator indicative of an overall activity of the subjectusing:

-   -   a) the at least one muscle indicator; and,    -   b) at least one of:        -   i) a cardiac indicator indicative of cardiac activity of the            subject; and,        -   ii) a respiratory indicator indicative of respiratory            activity of the subject.

It will be appreciated that the broad forms of the invention and theirrespective features can be used in conjunction, interchangeably and/orindependently, and reference to separate broad forms is not intended tobe limiting.

BRIEF DESCRIPTION OF THE DRAWINGS

An example of the present invention will now be described with referenceto the accompanying drawings, in which:—

FIG. 1A is schematic diagram of a first garment for use in monitoringmuscle activity of a biological subject;

FIG. 1B is schematic diagram of a second garment for use in monitoringmuscle activity of a biological subject;

FIG. 2 is a flow chart of an example of a method for monitoring muscleactivity of a biological subject;

FIG. 3A is a schematic diagram of a first example of a system for use inmonitoring muscle activity of a biological subject;

FIG. 3B is a schematic diagram of a second example of a system for usein monitoring muscle activity of a biological subject;

FIG. 4 is a flow chart of an example of a method for preparing thesystem to monitor muscle activity of a biological subject;

FIGS. 5A and 5B are a flow chart of a specific example of a method formonitoring muscle activity of a biological subject using the system ofFIG. 3 ;

FIG. 6 is a flow chart of an example of a method for determining anintramuscular indicator;

FIG. 7 is a flow chart of an example of a method for determining anintermuscular indicator;

FIG. 8 is a flow chart of an example of a method for determining anefficiency indicator; and,

FIG. 9 is a flow chart of an example of a method for determining afatigue indicator.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Examples of garments for use in monitoring muscle activity of a subjectare shown in FIGS. 1A and 1B.

The garments 110, 120 each include a number of arrays of electrodes 111,121 positioned on the garment 110, 120 so that when the garment is wornby a subject in use, the electrodes contact skin of the subject andgenerate electrical signals indicative of electrical potentials withinrespective muscles of the subject. In this example, the garments are inthe form of a shirt 110 for covering at least the torso and parts of thearms of the user and pants 120 for covering at least the groin and upperlegs of the user, although other suitable arrangements can be used aswill be described in more detail below.

In use, the electrodes 111, 121 are electrically connected to at leastone processing device that operates to process signals and determine atleast one muscle activity indicator. The at least one processing devicecould be of any suitable form, and could include a wearable custom oroff the shelf processing device and/or a suitably programmed generalpurpose processing system, such as a computer system, smart phone,smartwatch, tablet or the like.

An example of a method of use of the system will now be described withreference to FIG. 2 .

In this example, at step 200, the subject wears the garment(s) andperforms activities at step 210. The activities could be of any suitableform depending on the preferred implementation or use. For example, ifthe subject is an athlete or sports person, the activities could includeexercises, participating in a sporting event, training or the like.Alternatively, the subject may be undergoing monitoring as part of amedical assessment, for example to assess muscle strength and movementpatterns in individuals having muscular or neurological conditions suchas myolysis, myasthenia gravis, muscular dystrophy, or the like, inwhich case the activities could include day-to-day activities, definedsequences of movements, exercises or the like.

At step 220, the electrodes 111, 121 generate electrical signals basedon electrical activity within the subject's muscles, with the processingdevice processing these signals at step 230 to determine a muscleactivation for parts of the respective muscles. The muscle activation isindicative of the degree of electrical activity within the respectiveparts of the muscle and in particular at least one of the frequencyand/or magnitude of activation, and therefore corresponds broadly to theamount of work being performed by the respective part of the muscle.Thus, signals from different pairs of electrodes within each array areused to determine a degree of muscle activation for different parts ofmuscles within each muscle or muscle group.

At step 240, the processing device uses the muscle activation todetermine at least one muscle indicator indicative of muscle activity ofthe subject, with the indicator being optionally displayed at step 250.

The indicator can be of any suitable form, and can include a number ofdifferent indicators examining different aspects of muscle activity. Forexample, the system can be used to determine any one or more of anintramuscular indicator indicative of muscle activation within a muscle,an intermuscular indicator indicative of a relative muscle activation ofcontralateral muscles on contralateral limbs, an efficiency indicatorindicative of the relative efficiency of muscle activation of muscleswhen performing a task, and a muscle fatigue indicator indicative of amuscle fatigue. However, these examples are not intended to be limitingand additional and/or alternative indicators could be used depending onthe preferred implementation. Specific example indicators and techniquesfor their derivation will be described in more detail below.

The above described steps can be performed periodically or continuouslyas a subject performs exercise. For example, the system couldcontinuously monitor muscle activity, and display indicators in realtime, allowing an individual to use these as feedback while performingactivity. Additionally and/or alternatively, indicators and raw datacould be stored, allowing these to be subsequently reviewed after theactivity has been performed.

In any event, it will be appreciated that the indicators can be used toassess a wide range of different aspects of muscle activity, includingfor example whether the subject is using their muscles effectively,whether the muscles are functioning as expected/required, whether thesubject is fatigued, whether the muscles are injured and/or at risk ofinjury, or the like.

Accordingly, the above described system and process allows a subject'smuscle activation to be monitored, whilst the subject performs differentactivities, in turn allowing a muscle activity indicator to bedetermined. By allowing this to be performed using garmentsincorporating arrays of electrodes, this allows monitoring to beperformed during a range of different activities, including sport,exercise and/or day-to-day activities, without impeding the subject.Additionally, through suitable arrangement of the electrodes, thisallows information regarding the activation of different parts ofdifferent muscles to be monitored, allowing a range of differentindicators to be derived, which can in turn be used to assess musclefunction. This can be used for medical purposes, for example as part ofthe diagnosis and/or treatment of medical conditions, as well as foractivity monitoring, for example to examine muscle activity of aparticipant in a sporting event to ensure the participant is functioningoptimally.

As part of this, it will be appreciated that the indicator could befurther used as part of general fitness tracking, for example bymonitoring total muscle activity during a workout, which in turn canallow a more accurate assessment of calories burned to be made.

A number of further features will now be described.

The electrodes are typically integrally formed within the garment, andcould include any suitable conductive dry electrodes, which may forexample be woven into the garment as conductive fabric electrodes. Inone particular example the electrodes are silver plated nylonelectrodes, or the like, examples of which are described inWO2014/080403. However, it will be appreciated that any conductive ormetal coated fabric or nanowire could be used. For example, theelectrodes could be silver plated nanowire electrodes provided on anelastomeric substrate, such as polydimethylsiloxane (PDMS), similar tothose described in “Wearable silver nanowire dry electrodes forelectrophysiological sensing” by Amanda C. Myers, He Huang and Yong Zhuin RSC Adv., 2015, 5, 11627-11632|11627. This allows the electrodes toremain as part of the garment whilst the garment is washed, making thesystem readily useable in a variety of situations. Alternatively,electrodes could be screen printed or applied using any other suitabletechnique and could include using a stretchable resin base material witha conductive paste to provide a flexible electrode.

The garment is typically made of an elasticated material, which helpsurge the electrodes against the subject's skin, avoiding the need forany adhesive, conductive gel, or the like, whilst ensuring goodelectrical contact between the electrodes and the subject's tissue,which is in turn important in ensuring accurate measurements arecollected. The garment can be made of any suitable material, but istypically made of a mixture of polyamides and elastane, in the form ofan elasticated compressive garment, similar to those marketed under thetrade name Skins™. This is particularly beneficial as this allows thesubject to simply wear the garment as though it were part of theirnormal sporting attire, whilst also providing the benefit of suchgarments. However, it will be appreciated that other materials could beused such as polyester, or the like.

Each array of electrodes typically includes at least two electrodes, andmore typically a plurality of electrodes arranged in a grid. Theelectrodes typically have a surface area that is between 0.5 cm² and 3.0cm², between 0.75 cm² and 1.5 cm², about 0.75±0.25 cm², about 1.0±0.25cm², about 1.25±0.25 cm², about 1.5±0.25 cm², about 1.75±0.25 cm², about2.0±0.25 cm², about 2.5±0.5 cm², and more typically about 1 cm². Theelectrodes can be of any shape and could include circular electrodeshaving a diameter of between 0.5 cm and 1.5 cm, and more typically about1 cm. The electrodes are typically separated by between 0.5 cm and 2.0cm, between 0.75 cm and 1.75 cm and between 1.0 cm and 1.5 cm, about0.75±0.25 cm, about 1.0±0.25 cm, about 1.25±0.25 cm, about 1.5±0.25 cm,or approximately 2 cm between centres of adjacent electrodes, althoughalternative spacings could be used depending on the required resolutionof the measurements. In this regard, it will be appreciated thatdifferent electrode sizes and/or spacings could be used to vary theresolution of the measurements, allowing measurements to be performed upto and include of muscle fibres connected to a single neural pathwayending. This allows the firing of individual neural muscle connectionsto be monitored. Further issues regarding electrode sizing and spacingcan be found in “The Effects of Electrode Size and Orientation on theSensitivity of Myoelectric Pattern Recognition Systems to ElectrodeShift” by Aaron J. Young published in IEEE TRANSACTIONS ON BIOMEDICALENGINEERING, VOL. 58, NO. 9, September 2011.

Each electrode in the electrode array is electrically connected to aconnector, for example via a respective conductive path running from theelectrode to the connector. The conductive path can be formed of anyappropriate conductive material, but in one example is made ofconductive nanowires woven into the fabric. Such nanowires, typicallymade of coated nano tubes, are particularly advantageous as they arethin and flexible, allowing the garment to maintain its wearablecharacteristics, whilst being strong, resulting in a greater lifespan.

The connector is used for electrically connecting the electrodes to theat least one processing device. In this regard, the at least oneprocessing device can be mounted in a pocket 112, 122 provided on thegarment, with the connector being provided at least partially within thepocket. This allows the processing device to be easilyconnected/disconnected to the electrodes and hence removed from thegarment as required, for example to allow the garment to be washed. Thiscould be achieved using a “clip-in” arrangement, so that the processingdevice connects to the connector upon insertion into the pocket,although any suitable arrangement could be used.

As shown in FIGS. 1A and 1B, the garment can include pants 120 forcovering at least the groin and upper legs of the user or a shirt 110for covering at least the torso of the user. It will be appreciated thatother suitable arrangements could be used, such as fully body torso orleggings.

Each array of electrodes is typically aligned with a respective muscleor muscle group, including but not limited to any one or more oftrapezius, rhomboids, latissimus dorsi, erector spinae, rotator cuff,forearm extensors/flexors, tibialis anterior/posterior, thoracicparaspinals, lumbar paraspinals, biceps, triceps, quadriceps,hamstrings, adductors, gluteals, calves, abdominals, deltoids andpectorals. It will be appreciated that the particular configuration usedmay depend on the intended application, and in particular which musclesare of interest from the perspective of monitoring.

The muscle activation can be determined from the signals generated bythe electrodes in any suitable manner. For example, the muscleactivation can be indicative of at least one of a magnitude andfrequency of the signals, and can be determined using appropriatesignals processing techniques, such as Fourier analysis or the like. Itwill be appreciated from this that the signals are Electromyography(EMG) signals, and accordingly appropriate signal processing techniquesused for EMG could be employed.

Having determined the muscle activation, additional processing isperformed in order to determine the indicators. The nature of theprocessing will depend on the type of indicator being derived.

For example, to determine an intramuscular indicator the processingdevice typically determines an average muscle activation, compares themuscle activation of parts of the muscle to the average muscleactivation and determines an intramuscular indicator at least in partusing results of the comparison. Thus, this will identify if activationis relatively constant across the entire muscle, or whether somedistinct parts of the muscle are undergoing greater or lesseractivation, which can be useful in identifying potential injuries and/ormuscle damage.

To determine an intermuscular indicator, the processing device comparesthe muscle activation of each muscle in a pair of contralateral musclesand then determines the intermuscular indicator at least in part usingresults of the comparison. Thus, this examines whether contralateralmuscles, such as the hamstrings in each leg, are activating to a similardegree, or whether one muscle is being favoured over the other, whichcan in turn be indicative of injury, or an imbalance in muscle use.

To determine an efficiency indicator, the processing device candetermine a muscle activation pattern indicative of the muscleactivation of each of a number of muscles, compare the muscle activationpattern to a reference muscle activation pattern and, determine anefficiency indicator at least in part using the results of thecomparison. Thus, this can use predefined muscle activation patterns toassess whether the subject's muscles are activating in an optimumpattern. The predefined muscle activations are typically defined basedon a range of factors, such as the activities being performed, andcharacteristics of the subject.

Thus, the processing device typically determines an activity beingperformed by the subject and selects one of a number of predefinedreference activation patterns at least partially in accordance with thedetermined activity. In this regard, it will be appreciated that adifferent activation pattern would be expected if the subject isperforming squats, as opposed to running or jumping. Accordingly, bydetermining the activity being performed, this allows the processingdevice to select the most appropriate reference activation pattern. Theprocessing device can determine the activity being performed using anysuitable approach, such as analysing muscle activation patterns and/orin accordance with user input commands, or the like. Thus, theprocessing device can monitor the muscle activation patterns toautomatically determine the particular activity being performed, withoutrequiring input from the user. This would typically be performed bycomparing measured muscle activity patterns to defined patternsrepresenting different activities.

Additionally, the reference muscle activation pattern can be selectedbased on subject parameters, defining characteristics of the subject,such as a subject age, a subject sex, a subject weight, a subject heightand a subject fitness level. Thus, different reference patterns could beestablished for different groups of individuals, allowing the muscleactivation pattern of the subject to be compared to patterns of similarindividuals performing similar activities. Thus, the activity patternrecorded for other individuals can be used to establish an idealisedbaseline as the reference activity pattern, with the subject's activitybeing compared to this to identify deviation from the baseline.

Additionally and/or alternatively the reference activation pattern caninclude a previous recorded activation pattern for the subject. This canbe useful, for example, to monitor improvement and/or worsening ofmuscle activation during certain activities. This can be used toidentify improvements as a result of training, medical intervention orrehabilitation, or problems arising, for example due to progression ofmuscle related disorders. Such prior activation patterns could be storedas part of a user profile, stored either locally on the processingdevice, or remotely, for example in a cloud or network based store.

The processing device can determine a fatigue indicator by determining acurrent muscle activation pattern indicative of the muscle activation ofeach of a number of muscles, determining previous muscle activationpatterns, identifying a historical activation based on at least one of amean and maximum of the previous muscle activation patterns, comparingthe current muscle activation pattern to the historical activationpattern and determining a fatigue indicator at least in part using theresults of the comparison. Thus, this allows changes in muscleactivation over time to be used to determine a level of a fatigue. Inone example, this process is performed at least partially based on thefrequency of muscle activation, which is a known indicator of musclefatigue, as will be described in more detail below.

It will be appreciated form the above that the system can use a widerange of different analysis techniques in order to analyse the muscleactivation signals and determine one or more muscle indicators. Thiscould include pattern recognition, in which muscle activation patternsare compared to reference or previously measured activation patterns.Alternatively, this could involve performing component analysis, such asprinciple component analysis (PCA) in order to identify components ofthe muscle activation signals, and hence derive the indicatorstherefrom. For example, this could involve analysing signal amplitude,frequency, gradients, or the like, and using these to determine themuscle indicators.

Typically the processing device generates a representation at leastpartially based on the indicator and causes the representation to bedisplayed to a user. This allows the one or more indicators to bedisplayed to a user, allowing the user to view the current muscleactivation of the subject. In this regard, it will be appreciated thatthe subject could be the user, although this is not essential andalternatively the user could be a third party that is monitoring orobserving the subject. For example, the user could be a medicalpractitioner reviewing monitoring the muscle health or activity levelsof a patient. Alternatively, the user could be a coach or trainermonitoring the muscle activity of a trainee, such as an athlete or thelike.

The representation could be of any suitable form but typically includesan alphanumeric indication of the indicator, a graphical representationof a muscle activation pattern for at least one muscle and/or agraphical representation of results of a comparison of a muscleactivation pattern to a reference muscle activation pattern. Differentrepresentations could be used for different indicators, and typicallythe user would have the ability to select a desired representation type.

Whilst the system can use a single processing device, such as a singleworn processing system, more typically functionality is distributedbetween multiple processing devices. In this case, the system typicallyincludes a first electronic processing device attached to or worn by thesubject that acquires signals from the sensors and at least partiallyprocesses the signals and a second processing device that wirelesslycommunicates with the first processing device and displays arepresentation at least partially based on the indicator. This allowsmonitoring of the subject to be performed remotely, without impeding thesubject. This also allows more computationally expensive operations tobe handled remotely to the subject, minimising the hardware requirementsof the device worn by the user.

In one particular example, the first processing device is part of ameasuring device including a voltage sensor coupled to the electrodesfor sensing electrical potentials between pairs of electrodes and atleast one processing device coupled to the voltage sensor for receivingsignals indicative of the sensed voltages, and at least partiallyprocessing these, for example to determine signal parameters. Themeasuring device is typically mounted within the pocket, and is adaptedto communicate with a separate remote second processing device, forexample forming part of a host device, such as a smart phone, tablet orthe like, allowing representations of the indicator to be viewedthereon.

From this it will be appreciated that the measuring device can be alightweight portable battery operated unit that is worn by the subjectduring activity, with the host device being provided remotely allowingthe muscle activity of the subject to be monitored.

The voltage sensor typically includes a differential amplifier foramplifying analogue electrical signals obtained from a pair ofelectrodes and an A/D convertor for converting an amplified differentialvoltage into a digital voltage signal, the digital voltage signal beingprovided to the at least one processing device for processing. Themeasuring device can also include a filter for filtering electricalsignals, for example using an analogue anti-aliasing front end filter,or a bandpass filter in the digital domain to remove extraneous noise orother signal components. The measuring device can include a switchingdevice for selectively coupling a single voltage sensor to respectivepairs of electrodes in each array, or alternatively, multiple voltagesensors could be provided, with each being adapted to measure signalsfrom a respective pair of electrodes. This allows readings to beobtained from different pairs of electrodes within each array, with thisbeing controlled by the processing device within the measuring device.

The system can also include additional sensors to determine otherphysiological parameters. For example, the system can include an ECGsensor for sensing cardiac activity of the subject, with the processingdevice acquiring signals from the ECG sensor and determining a cardiacindicator indicative of cardiac activity of the subject. Similarly, thesystem can include a respiratory sensor for sensing respiratory activityof the subject, in which case the processing device typically acquiressignals from the respiratory sensor and determines a respiratoryindicator indicative of respiratory activity of the subject.

When cardiac and/or respiratory indicators are determined, theprocessing device can determine an activity indicator indicative of anoverall activity of the subject using the at least one muscle indicatorone or more of the cardiac indicator and respiratory indicator.

A specific example of the electronic components of the system will nowbe described in more detail with reference to FIG. 3A.

In this example, as previously described the system 300 includes ameasuring device 310, which is adapted to be coupled to the garment andworn by the user, and a host device 320, which is in communication withthe measuring device, to allow indicators to be displayed thereon.

In this example, the measuring device 310 includes a microprocessor 311,coupled to a memory 312 and an external interface 313, such as awireless communications interface for communicating with the host device320.

The measuring device 310 includes a switching device 314, such as a dualband multiplexer, which is coupled to respective electrode arrays 331,332, 333, via a port 316 and corresponding connector 330 provided on thegarment. Although three electrode arrays are shown, this is for thepurpose of illustration only, and in practice any number of electrodearrays may be provided, depending on the preferred implementation.

The switching device 314 is also coupled to a voltage sensor 315,allowing signals from respective pairs of electrodes within the arraysto be provided thereto. The voltage sensor typically includes adifferential amplifier 315.1, for amplifying a potential differenceacross the pair of electrodes and an analogue-to-digital convertor (ADC)315.2 for digitising the resulting potential difference signal. Anoptional filter (not shown) is also provided for filtering the signalsfor example using a bandpass filter, to remove any signal componentsfrom other sources, such as noise in the leads, or other biologicalsignals, such as ECG signals or the like. Accordingly, in use, thevoltage sensor 315 amplifies the potential difference between theelectrodes in the respective pair, and generates an analogue voltagesignal, which is then filtered and digitised before being provided tothe processor 311 for analysis.

In use, the processor 311 controls the switching device 314 to connectthe differential amplifier to respective pairs of electrodes within agiven electrode array 331, 332, 333, based on a defined measurementprotocol. The measurement protocol typically defines a sequence of pairsof electrodes from which measurements should be taken, and may be storedin the memory 312 and selected depending on the desired outcome, as willbe described in more detail below.

An alternative configuration is shown in FIG. 3B, in which multiplevoltage sensors 315 are provided, with each being coupled to arespective pair of electrodes. In practice this configuration could beprovided using a sequence of daisy chained ADCs 315.2, although anysuitable configuration could be used. It will be appreciated that thisconfiguration allows muscle activation signals to be measured frommultiple pairs of electrodes in parallel, allowing measurements formultiple muscles and parts of muscles to be performed substantiallysimultaneously. This reduces overall measurement time, allowing repeatedmeasurements to be performed at a higher rate, whilst also assistingwith analysis of the signals, by allowing signals captured at anidentical time to be analysed.

In each case, the measuring device 310 may also include a cardiac signalsensor 342 coupled to ECG electrodes 341, via the connector 330 and port316. The cardiac signal sensor 342 typically includes an amplifier 342.1and an analogue-to-digital convertor (ADC) 342.2, as well as an optionalfilter (not shown). Similarly the measuring device can include arespiratory signal sensor 352 coupled to a respiratory sensor 351 viathe port 316 and connector 330. The nature of the respiratory sensorwill vary depending on the preferred implementation and could include asensor for measuring tension in an elastic belt extending round thechest or abdomen of the subject, or an inductance sensor that includes aconductive loop of wire attached to the subject. Example commercialinductance sensors include Philips Respironics zRIP inductiverespiratory effort sensors. In either case, the respiratory signalsensor 352 typically includes an amplifier 352.1 and ananalogue-to-digital convertor (ADC) 352.2, as well as an optional filter(not shown).

It will be appreciated that the cardiac and respiratory signal sensors342, 352 are not essential, and in particular would only be requiredwhen used in conjunction with a garment, such as the shirt garment 110including respective ECG electrodes 341 or respiratory sensor 351.Typically however standard measuring devices would be used inconjunction with the pants and shirt garments 120, 110, with the cardiacand respiratory signal sensors 342, 352 being unused if not required,thereby allowing common componentry to be used for the pant and shirtbased measuring devices.

In use, the microprocessor 311 executes instructions in the form ofapplications software stored in the memory 312 to allow communicationwith the host device 320, as well as to control operation of theswitching device 314, and at least partially process signals from thevoltage sensor 315, the cardiac signal sensor 342 or respiratory signalsensor 352, providing an output based on the processed signals to thehost device.

It will be appreciated from the above, that the measuring device 310 caninclude any suitable electronic processing device such as amicroprocessor, microchip processor, logic gate configuration, firmwareoptionally associated with implementing logic such as an FPGA (FieldProgrammable Gate Array), or any other electronic device, system orarrangement.

The measuring device 310 can also include other ancillary sensorsystems, such as a GPS (Global Position System), accelerometers,gyroscopes or the like, allowing additional parameters, such as movementof the subject to be sensed and used in determining indicators and/ormonitoring activity.

The host device 320 typically includes a microprocessor 321, a memory322, an input/output device 323, such as a keyboard and/or display, andan external interface 324, interconnected via a bus 325 as shown. Inthis example the external interface 324 can be utilised for connectingthe host device 320 to peripheral devices, such as the measuring device310, as well as other devices, such as communications networks,databases, other storage devices, or the like. Although a singleexternal interface 325 is shown, this is for the purpose of exampleonly, and in practice multiple interfaces using various methods (eg.Ethernet, serial, USB, wireless or the like) may be provided.

In use, the microprocessor 321 executes instructions in the form ofapplications software stored in the memory 322 to allow communicationwith the measuring device 310, for example to control operation of themeasuring device 320, to receive outputs therefrom, and to at leastpartially process outputs to create and display representations of oneor more indicators.

Accordingly, it will be appreciated that the host devices 320 may beformed from any suitable processing system, such as a suitablyprogrammed PC, Internet terminal, lap-top, or hand-held PC, and in onepreferred example is either a tablet, or smart phone, or the like.However, it will also be understood that the host device 320 can be anyelectronic processing device such as a microprocessor, microchipprocessor, logic gate configuration, firmware optionally associated withimplementing logic such as an FPGA (Field Programmable Gate Array), orany other electronic device, system or arrangement.

Examples of the processes for monitoring muscle activity will now bedescribed in further detail. For the purpose of these examples it isassumed that the host device 320 is a smart phone, tablet, smartwatch orother similar computing device that executes a software application thatallows for communication with one or more measuring devices 310, each ofwhich is associated with a respective garment.

However, it will be appreciated that the above described configurationassumed for the purpose of the following examples is not essential, andnumerous other configurations may be used. It will also be appreciatedthat the partitioning of functionality between the host devices 320, andthe measuring devices 310 may vary. For example, the operation of themeasuring device 310 could be controlled by a user via a user interfacedisplayed on the measuring device, allowing the measurement process tobe performed, with data indicative of measured signals being pushed tothe host device, thereby allowing measurements to be performed withoutrequiring the host device. It will also be appreciated that the hostdevice could be connected to one or more other processing systems, suchas part of a cloud or other distributed architecture.

An example of a process for configuring the system for performing musclemeasurement will now be described with reference to FIG. 4 .

Initially, at step 400 the subject wears one or more garment(s), withrespective measuring device(s) being connected to each garment at step405. Thus, the connector 330 of each garment would be plugged into theport 316 of the respective measuring device 310, with this then beingsecured in the pocket of the garment.

At step 410, the measuring device(s) are connected to the host device320. Thus can be achieved using any suitable technique, such as using awireless communications protocol, such as Bluetooth™, or the like.Accordingly, the measuring device 310 can be turned on, and a softwareapplication on the host device launched, with the host device 320 beingcontrolled by the application to cause the host device 320 to detect andconnect to any active measuring devices 310 within range. It will beappreciated that as part of this a pairing procedure may be required toensure the host device 320 is connecting to the correct measuringdevice(s) 310. As such pairing procedures are known in the art, thiswill not be described in any detail.

At step 415, the host device checks the connection with each measuringdevice 310, reconnecting at step 410 in the event that the connection isnot operating successfully. This can be repeated until a successfulconnection is established, allowing the remaining procedures to beperformed.

At step 420, the host device 320 can be used to assign a respectivemeasuring device 310 to a particular subject. This is typically achievedby creating an association between a unique identifier of each measuringdevice 310, and an identifier associated with each subject, such as aname, or other suitable identifier. This allows a single host device tobe used with measuring devices 310 associated with multiple subjects, sothat a number of different subjects can be monitored using a single hostdevice. This is particularly useful for scenarios such as team sports,where a coach or trainer could use a single host device to monitor themuscle activity of each team member. Alternatively, a medicalpractitioner could monitor many patients at once such as in a rehab orhospital environment.

Accordingly, the host device 320 can be used to present the user with alist of connected measuring devices 310, allowing the user to allocatethese to respective individuals. Information regarding the associationis then typically stored in a store, such as the memory 322, a remotedatabase, or the like.

This process can also be used to ensure subject specific data is usedduring the analysis process. For example, a profile of each subject canbe established, specifying subject characteristics, such as age, sex,weight, height, details of injuries, medical conditions and/orinterventions, or the like. This information can be used when analysingrecorded measurements, as will be described in more detail below.

At step 425, the user can optionally select an activity to be performed,allowing this information to be used in controlling the monitoringand/or analysis of muscle activity. The activities are generallypredefined, for example by a supplier of the system and/or a user ormedical practitioner or the like, and may be stored in a referencedatabase, or the like, allowing the host device 320 to display a list ofpredefined activities. Alternatively, the user can custom defineactivities, for example specifying the type of activity and anyrequirements associated with the monitoring and/or analysis process tobe used.

In the case of the monitoring process, the defined activity can be usedto control the relative degree of monitoring of different muscle groups.For example, when performing squats, the primary muscles used are legmuscles. Thus, monitoring can be controlled to increase the sample ratefor the leg muscles, whilst decreasing the sampling rate for lesser usedmuscles, such as arm muscles. This can be used to maximise theresolution of data collection for the primary muscles used in thespecified activity.

In terms of analysing results, knowledge of the activity performed canbe used to select a specific reference muscle activity pattern, whichcan be used when determining the indicators. For example, this allowsthe muscle activity of the subject collected whilst performing squats tobe compared to an idealised muscle activity pattern for an individualwith similar physical characteristics. This also allows signals to beanalysed using appropriate techniques, such as magnitude and/orfrequency analysis, depending on the indicator to be determined.

At step 430, the measurement process is triggered, for example by havingthe user select a “record now” option presented on the host device. Atthis point, the host device 320 communicates with the measuring device310, causing the measuring device 310 to commence measurement of muscleactivity. As part of this process, the host device 320 can transferinstructions to the measuring device 310, to control the measurementprocess, for example, instructing the measuring device to perform aparticular measurement protocol. Once measurement has commenced, anindication of this can be provided, for example via the host device 320,or through a visual or audible indication on the measuring device 310,allowing the subject to be notified that activity can be commenced atstep 435.

It will be appreciated however that connecting the measuring device tothe host device as set out in steps 410 to 425 could be performed afteran activity has been recorded. In this instance, the user could simplyactivate the measuring device, for example using a suitable input buttonprovided on the device, causing measurements to be performed. In thiscase, connection to the host device may only occur after themeasurements have been recorded, or could be performed automaticallyduring the activity, and reference to connection of the measuring andhost devices prior to commencing activity is not intended to belimiting.

The process of monitoring muscle activity after commencing activity willnow be described with reference to FIGS. 5A and 5B.

In this example, at step 500, the measuring device 310 determines themeasurement protocol to be used for the sequence of measurements. Themeasurement protocol is typically retrieved from memory 312 based oninstructions provided by the host device 320, as described above withrespect to FIG. 4 , although alternatively may be received directly fromthe host device 320, depending on the preferred implementation.Alternatively, the measurement protocol could be a standard protocolimplemented when the measuring device is activated, or could be selectedfrom protocols stored locally in the memory 312 based on manual inputcommands, for example in the event the measurement process is triggeredwithout using the host device 320.

At step 505, the processor 311 selects a next pair of electrodes fromwhich a measurement is to be taken, and controls the switching device314 accordingly at step 510, to thereby couple the respective pair ofelectrodes to the voltage sensor 315. It will be appreciated that thesesteps are not required in the event that the apparatus of FIG. 3B isused, in which case measurements are performed for each pair ofelectrodes simultaneously.

The potential difference between the electrodes is amplified by theamplifier 315.1 at step 515, before being filtered and digitised at step520. It will be appreciated that the measurement is typically performedover a predetermined time period, such as a few milliseconds, allowingthe frequency and magnitude of the potential difference to be captured.The exact time period used will depend on the preferred implementation,and/or measurement protocol, as will be appreciated by persons skilledin the art.

The digitised voltage signals are provided to the processor 311, whichtypically at least partially analyses the signals to determine signalparameters, which are then stored in the memory 312 at step 525. It willbe appreciated that the signals themselves can also be stored, althoughthis is not necessary and hence will typically depend on storageavailability.

The nature of the processing performed by the processor 311 will varydepending on the preferred implementation, and can include for exampleperforming a Fourier analysis to determine the magnitude of the voltagebetween electrodes for different frequency components within themeasured signal. In this regard, the measurement protocol can define theprocessing to be performed and in particular any signal parameters thatare to be determined, such as frequency components of interest andexamples of types of analysis that can be performed are described in“Techniques of MG signal analysis: detection, processing, classificationand applications” by M. B. I. Raez, M. S. Hussain, 1 and F. Mohd-Yasinin Biol Proced Online. 2006; 8: 11-35.

In any event, at step 530 the processor 311 determines if all requiredmeasurements have been completed, and if not returns to step 510 tocontrol the switching device and record measurements for the next pairof electrodes. Again it will be appreciated that this is not required inthe event that measurements are performed on all pairs of electrodessimultaneously.

At steps 535 and 540 the processor 311 will optionally record ECG andrespiratory signals from the cardiac and respiratory sensors in asimilar manner. It will be appreciated that in practice this istypically performed in parallel with the process described in steps 510to 530, so that cardiac and respiratory signals are recordedconcurrently with collection of muscle activity signals.

Once muscle activity and optionally ECG and respiratory signals havebeen recorded, these can be used to determine indicators. This processcan be performed in a variety of manners, and could include calculatingthe indicators in the processor 311. More typically however, the signalparameters determined at step 525 are uploaded to the host device foranalysis at step 545. This allows processing to be distributed betweenthe measuring device 310 and host device 320 and also avoids the needfor references and calculation techniques to be stored on the measuringdevice. However, this is not essential and any suitable distribution ofprocessing can be used.

Whilst upload of information can be performed once the measurementprocess has been concluded, more typically this is performed whilstcollection of data continues, with the processor 311 returning to step505 to select a next electrode pair, allowing indicators to becalculated and displayed dynamically as activities are ongoing. This isparticularly useful in monitoring the ongoing effect of the activitiesbeing performed on muscle activity. In particular, this allows real-timefeedback to be provided to the subject as the activities are performed.

At step 550, the host device 320 determines various indicators,depending for example on the measurement protocol being performed, andexamples of the derivation of specific indicators will be described inmore detail below.

Once indicators have been determined, at step 555, the host device 320generates a representation of the indicators, allowing this to bedisplayed to a user. The nature of the representation will varydepending on the preferred implementation, user settings and the natureof the indicator.

In one example, the representation can include a simple alphanumericindicator, indicative of a measured activity for one or more musclesand/or muscle groups. However, more typically the representationincludes a graphical representation of a human body, illustrating one ormore muscle groups, and showing visual indications of the indicatorsthereon. This could include colour coding of parts of individualmuscles, or muscle groups to illustrate a level of activity relative toa baseline or other reference, showing a graph indicative of the levelof ability, or the like. It will be appreciated that by havingindicators indicative of muscle activity measured and displayed in realtime can help provide useful feedback to the subject performing theactivity, in particular allowing the individual to assess whether theactivity is being performed effectively, and potentially to identify theonset of fatigue and/or the potential for injury.

An example of the process for determining an intramuscular indicatorwill now be described with reference to FIG. 6 .

In this example, at step 600 a next muscle or muscle group is selected,with an average activation for the respective muscle or muscle groupbeing determined at step 605. In this example, the activation istypically based on the magnitude of the potential difference betweenpairs of electrodes, averaged for each pair of electrodes for the givenmuscle or muscle group. It will be appreciated that averaging could beperformed in any appropriate manner, and in one example this could beachieved based on an average derived from measurements made between endpoints, and between end and mid points of the muscle. This reduces thenumber of measurements required to determine an average, whilst stillallowing a reasonable accurate average to be determined.

At step 610, the muscle activation for each part of the muscle or musclegroup, as determined based on the magnitude of the potential differencebetween a pair of electrodes, is compared to the average activation. Theresults of the comparison are used to determine the intramuscularindicator at step 615, specifically by identifying parts of the muscleor muscle group that are demonstrating an activation beyond one or morestandard deviations of the average cell-cell muscle activation. At step620, it is determined if all muscles are complete, and if not theprocess returns to step 600, otherwise the process ends at step 625.

The intramuscular indicator can be of any form and is generally used toidentify parts of the muscle or muscle group which are demonstratingabove or below average activation, which is in turn used to identifypotential muscle damage. For example, in the event that part of themuscle is damaged, this could be under activating, whilst overactivating parts of a muscle could indicate the potential for injury.

In one example, the indicator is used to generate a representation inthe form of a map of the respective muscle, with the location of over orunder active parts of the muscle being identified thereon. For example,this could include colour coding to indicate the degree of under or overactivation, as compared to the average activation.

An example of the process for determining an intermuscular indicatorwill now be described with reference to FIG. 7 .

In this example, at step 700 a next contralateral muscle pair isselected. In this regard, the contralateral muscle pair is a pair ofmuscles or muscle groups positioned on contralateral parts and typicallylimbs, of the subject's body.

At step 705 an average activation for each muscle in the pair isdetermined, with this again being performed by averaging the magnitudeof the potential difference for each pair of electrodes for therespective muscle or muscle group.

At step 710, the average activation for each muscle is compared, with adifference being used to determine the intermuscular indicator at step715. At step 720, it is determined if each pair is complete, and if notthe process returns to step 700. Otherwise, the process ends at step720.

In this instance, the intermuscular indication is indicative of anydisparate average activation between contralateral muscles, and is usedto identify any imbalance in muscle activation in the subject. It willbe appreciated that this indicator is generally only determined when theuser is performing an activity that places symmetrical loads on themuscles.

An example of the process for determining an efficiency indicator willnow be described with reference to FIG. 8 .

In this example, at step 800 a muscle activation for each muscle ormuscle group is determined. Again this is typically performed byaveraging the magnitude of the potential difference for each pair ofelectrodes for the respective muscle or muscle group.

At step 805, a muscle activation pattern is determined, with thistypically representing a proportion of the overall muscle activityattributable to each muscle.

At step 810, a reference activation pattern is selected. The referenceactivation pattern can be determined based on a study of individuals ina sample population when the individuals are performing the sameactivity as the subject. The individuals are typically selected to havesimilar physical characteristics, such as sex, ethnicity, age, weight,height, body mass index, or the like, and are typically assessed ashealthy individuals. Thus, it will be appreciated that the referenceactivation pattern represents an idealised activation pattern for thesubject when performing the given activity.

However, additionally and/or alternatively, the reference muscleactivation pattern could be defined by a user. For example, if the useris a practitioner, such as a physiotherapist, doctor, trainer, or thelike, they may wish to define a reference activation pattern for asubject to achieve an end goal. This could be part of a treatmentprogram, for example to assist in recovery from injury, or with a viewto improving strength or movement. In this instance, it will beappreciated that the practitioner might be better able to determine adesired activation pattern based on an understanding of the requirementsfor the subject, which is therefore more appropriate than a fixeddefined pattern. However, to assist in avoiding injury, the referencepatterns could be tailored within defined limits, allowing somevariation between subject goals or requirements to be accommodated,whilst ensuring the patterns that could be adverse to the subject areavoided.

As part of this, the system can allow different reference activationpatterns to be shared, so for example, if a practitioner develops apattern that is particularly effective at treating a particular injuryor condition, or achieving a particular training goal, this can beshared with other users.

However, it will be appreciated that the use of “standard” definedreference patterns can also assist in ensuring consistency in assessmentor treatment of subjects. This can ensure that biases inherent whendifferent individuals monitor or treat a subject, are overcome orobviated, maximising the chance of issues being appropriately identifiedand addressed.

An example muscle activation pattern when performing squats is shown inTable 1 below, with the numbers representing a relative level ofactivity, defined to sum to 1.

TABLE 1 Muscle Left Right Gluteals 0.4 0.4 Quadriceps 0.175 0.175Hamstrings 0.225 0.225 Adductors 0.1 0.1 Calf 0.1 0.1

At step 815, the measured activation pattern is compared to thereference activation pattern, with this being used to determine anefficiency indicator at step 820. The efficiency indicator could be usedto identify muscles or muscle groups that are over or under activatingcompared to the reference activation pattern, which in turn can identifyissues either with the subject muscles, and/or the technique the subjectis using when performing the respective activity. Thus, this can be usedto identify if the subject is performing the activity in the mostefficient manner.

An example of the process for determining a fatigue indicator will nowbe described with reference to FIG. 9 .

In this example, at step 900 a current muscle activation pattern isdetermined for the subject. In this example, the activation pattern istypically based on the frequency of muscle firing and/or the wavecomplex analogous to the QRS complex of an ECG signal.

At step 905, previous historical activation patterns recorded for thesubject, when performing the same activity, are determined, for exampleby retrieving these from a store, such as a memory, a database, or thelike.

At step 910, the previous activation patterns are analysed to identify amaximum and/or average historical activation pattern at step 915. Thecurrent activation pattern being compared to the historical maximumand/or average activation pattern at step 920, with deviations from theaverage and/or maximum being used to determine a fatigue indicator atstep 925. Thus, this allows the changes in activation, and in particularchanges in the frequency of activation over time to be monitored as asubject repeatedly performs a given activity, thereby allowing musclefatigue to be assessed.

The fatigue indicator could also take into account additional factors,such absolute or relative changes in heart and/or respiratory rate,distance travelled or other movements, as determined from appropriateones of the sensors.

It will also be appreciated that indicators indicative of a totalactivity for a defined period, such as a day, week, or specific workoutperiod, could be determined, and used as part of a fitness monitoringprogram. This could include using muscle activity together with overallindicators of movement, heart rate and respiration, to calculatecalories burned during an exercise program, with this being used as partof a broader fitness monitoring program, as will be appreciated bypersons skilled in the art.

Accordingly, the above described system allows measurements of muscleactivity to be performed through the use of wearable garmentsincorporating arrays of electrodes, which allow EMG signals indicativeof muscle activation to be monitored. This in turn allows muscleactivity to be measured whilst performing activities, including but notlimited to sporting activities, exercises, and/or day-to-day activities.Data collected can be analysed allowing a number of different indicatorsto be derived, which can in turn provide insights into the musclefunction and execution of the activities by the subject. This caninclude, but is not limited to identifying damage to muscles, imbalancein use of muscles, optimising the efficiency of muscle usage duringdefined activities, and detection of fatigue. The indicators can bedisplayed in real time as activities are performed and/or can berecorded and subsequently reviewed to allow for longitudinal study ofmuscle activity.

It will therefore be appreciated that the above described system can beused in a wide range of circumstances, including but not limited totraining of subjects for sporting activities, monitoring subject duringactivities to identify the potential for or onset of injuries, andstudying subjects in a medical context to identify muscle relatedconditions, such as muscle wastage, or the like.

Throughout this specification and claims which follow, unless thecontext requires otherwise, the word “comprise”, and variations such as“comprises” or “comprising”, will be understood to imply the inclusionof a stated integer or group of integers or steps but not the exclusionof any other integer or group of integers.

Persons skilled in the art will appreciate that numerous variations andmodifications will become apparent. All such variations andmodifications which become apparent to persons skilled in the art,should be considered to fall within the spirit and scope that theinvention broadly appearing before described.

The claims defining the invention are as follows:
 1. A system formonitoring a biological subject, the system including: a) a garmentincluding a number of arrays of electrodes positioned on the garment,wherein the arrays of electrodes are positioned on the garment so thatwhen the garment is worn by the biological subject, the electrodesconfigured to contact of the biological subject and generate electricalsignals indicative of electrical potentials within respective muscles ofthe biological subject, wherein each of the arrays of electrodesincludes a plurality of electrodes arranged in a grid; and, b) at leastone electronic processing device configured to: i) process signals fromthe electrodes in each of the arrays of electrodes to determine a muscleactivation for one or more parts of the respective muscles; ii) use themuscle activation to determine at least one muscle indicator indicativeof a muscle activity of the biological subject, wherein the at least onemuscle indicator is based on results of a comparison of a muscleactivation pattern for the muscle activation to a reference muscleactivation pattern which represents an idealised activation pattern forthe biological subject when performing a given activity; iii) generate arepresentation at least partially based on the at least one muscleindicator; and, iv) cause the representation to be communicated to auser.
 2. The system according to claim 1, wherein the electrodes are atleast one of: a) conductive fabric electrodes woven into the garment; b)dry electrodes provided in the garment; c) silver plated nylonelectrodes; and, d) silver plated nanowire electrodes.
 3. The systemaccording to claim 1, wherein each electrode at least one of: a) has asurface area that is at least one of: i) between 0.75 cm² and 1.5 cm′;ii) about 0.75+0.25 cm2: ii) about 1.0+0.25 cm2; iv) about 1.25+0.25cm2; v) about 1.5+0.25 cm2; vi) about 1.75+0.25 cm2; vii) about 2.0+0.25cm2; viii) about 2.5+0.5 cm2: ix) about 1 cm2, b) is spaced by at leastone of: i) between 0.5 cm and 2.0 cm; ii) between 0.75 cm and 1.75 cm;iii) between 1.0 cm and 1.5 cm; iv) about 0.75+0.25 cm; v) about1.0+0.25 cm; vi) about 1.25+0.25 cm; and, vii) about 1.5+0.25 cm; c) iselectrically connected to a connector, the connector being for couplingthe electrodes to the at least one processing device; and, d) iselectrically connected to the connector via nanowires woven into thegarment.
 4. The system according to claim 1, wherein the garment atleast one of: a) includes a pocket for receiving the at least oneprocessing device, a connector being provided at least partially withinthe pocket; b) includes pants for covering at least a groin and upperlegs of the biological subject; and, c) includes a shirt for covering atleast a torso of the biological subject; d) includes elasticatedmaterial to thereby urge the electrodes against the biological subject'sskin; and, e) is made of at least one of: i) polyamides; ii) polyester;and, iii) elastane.
 5. The system according to claim 1, wherein therepresentation includes at least one of: i) an alphanumeric indicationof the at least one muscle indicator; ii) a graphical representation ofthe muscle activation pattern for at least one muscle; and, ii) agraphical representation of the results of a comparison of the muscleactivation pattern to the reference muscle activation pattern.
 6. Thesystem according to claim 1, wherein the at least one muscle indicatoris an efficiency indicator, wherein the efficiency indicator isindicative of a relative efficiency of muscle activation of muscles whenperforming a task.
 7. The system according to claim 1, wherein each ofthe arrays of electrodes is aligned with a particular muscle or musclegroup and wherein the particular muscle or muscle group include at leastone of: a) trapezius; b) rhomboids; c) latissimus dorsi; d) erectorspinae; e) rotator cuff muscles (including supraspinatus, infraspinatus,subscapularis, teres minor/major); f) forearm extensors/flexors; g)tibialis anterior/posterior; h) thoracic paraspinals; i) lumbarparaspinals; j) biceps; k) triceps; l) Quadriceps; m) hamstrings; n)adductors; o) gluteals; p) calves; q) abdominals; r) deltoids; and, s)pectorals.
 8. The system according to claim 1, wherein the garmentincludes a plurality of the arrays of electrodes, and each of theplurality of the arrays of electrodes is aligned with a particularmuscle or muscle group.
 9. A system for monitoring muscle activity of abiological subject, the system including: a) at least one garmentincluding a number of arrays of electrodes positioned on the garment sothat when the garment is worn by the biological subject, the electrodesare configured to contact of the biological subject and generateelectrical signals indicative of electrical potentials within respectivemuscles of the biological subject, wherein each of the arrays ofelectrodes includes a plurality of electrodes arranged in a grid; and,b) at least one processing device that: i) determines a muscleactivation pattern indicative of a muscle activation of each of a numberof muscles; ii) compares the muscle activation pattern to a referencemuscle activation pattern; and, ii) determines an efficiency indicatorat least in part using results of the comparison, wherein the efficiencyindicator is indicative of a relative efficiency of muscle activation ofmuscles when performing a task.
 10. The system according to claim 9,wherein the at least one processing device: a) determines an activitybeing performed by the biological subject at least one of: i) byanalysing the muscle activation patterns; and, ii) in accordance withuser input commands; and, b) selects one of a number of predefinedreference activation patterns at least partially in accordance with thedetermined activity; and, c) compares the muscle activation pattern tothe selected reference muscle activation pattern.
 11. The systemaccording to claim 9, wherein the at least one processing device: a)determines a current muscle activation pattern indicative of the muscleactivation of each of the number of muscles; b) determines previousmuscle activation patterns; c) identifies an historical activationpattern based on at least one of a mean and maximum of the previousmuscle activation patterns; d) compares the current muscle activationpattern to the historical activation pattern; and, e) determines afatigue indicator at least in part using results of the comparison. 12.The system according to claim 9, wherein the system includes a measuringdevice, the measuring device including: a) a voltage sensor coupled tothe electrodes for sensing the electrical potentials between pairs ofelectrodes; and, b) the at least one processing device coupled to thevoltage sensor for receiving signals indicative of the sensed voltages.13. The system according to claim 12, wherein the voltage sensorincludes: a) a differential amplifier for amplifying analogue electricalsignals obtained from the pair of electrodes; and, b) an A/D convertorfor converting an amplified differential voltage into a digital voltagesignal, the digital voltage signal being provided to the at least oneprocessing device for processing.
 14. The system according to claim 12,wherein the measuring device includes at least one of: a) a filter forfiltering the electrical signals; b) an anti-aliasing front end analoguefilter; and, c) a digital bandpass filter.
 15. The system according toclaim 12, wherein the system includes: a) a first electronic processingdevice configured to be attached to or worn by the biological subjectthat: i) acquires the electrical signals from the voltage sensor; ii) atleast partially processes the electrical signals; and, b) a secondprocessing device that wirelessly communicates with the first processingdevice and displays a representation at least partially based on atleast one muscle indicator.
 16. The system according to claim 9, whereinthe system includes an ECG sensor for sensing cardiac activity of thebiological subject and wherein the at least one electronic processingdevice: a) acquires signals from the ECG sensor; and, b) determines acardiac indicator indicative of cardiac activity of the biologicalsubject.
 17. The system according to claim 9, wherein the systemincludes a respiratory sensor for sensing respiratory activity of thebiological subject and wherein the at least one electronic processingdevice: a) acquires signals from the respiratory sensor; and, b)determines a respiratory indicator indicative of respiratory activity ofthe biological subject.
 18. The system according to claim 9, wherein theat least one electronic processing device determines an activityindicator indicative of an overall activity of the biological subjectusing: a) at least one muscle indicator; and, b) at least one of: i) acardiac indicator indicative of cardiac activity of the biologicalsubject; and, ii) a respiratory indicator indicative of respiratoryactivity of the biological subject.
 19. A method for monitoring muscleactivity of a biological subject, the method including, in at least oneprocessing device: a) determining a muscle activation pattern indicativeof the muscle activation of each of a number of muscles; b) comparingthe muscle activation pattern to a reference muscle activation pattern;and, c) determining an efficiency indicator at least in part usingresults of the comparison, wherein the efficiency indicator isindicative of a relative efficiency of muscle activation of muscles whenperforming a task.